Tissue localizing and separating assembly

ABSTRACT

A tissue separator assembly has an elongate tubular member and a tissue separator device located at a distal end of the elongate tubular member. An elongate coupler extends through the lumen of the elongate tubular member and has a distal coupler end. A tissue localization assembly has an elongate member and a localization device located at the distal end of the elongate member. The localization device may be movable from a first, radially-contracted state to a second, radially-expandable state. The distal coupler end of the elongate coupler and the proximal end of the elongate tubular member of the localization assembly are joinable to one another to permit docking of the tissue localization assembly to the tissue separator assembly. Methods of use of this device are also described.

CROSS REFERENCE TO OTHER APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.10/374,583, filed Feb. 25, 2003, which is now U.S. Pat. No. 6,994,677,the entirety of which is hereby incorporated by reference.

This application is related to U.S. patent application Ser. No.10/045,657 filed 7 Nov. 2001 and entitled Tissue Separator Assembly AndMethod, which is abandoned. This application is also related to U.S.patent application Ser. No. 10/374,582, filed Feb. 25, 2003, entitledTissue Separating Catheter Assembly And Method, which is currentlypending and U.S. patent application Ser. No. 10/374,584, filed Feb. 25,2003, entitled Tissue Separating And Localizing Catheter Assembly, whichis abandoned. See also: (1) U.S. Pat. No. 6,179,860 issued 30 Jan. 2001and entitled Target Tissue Localization Device And Method, (2)International Publication No. WO 00/10471 published 2 Mar. 2000 andentitled Target Tissue Localization Device And Method, (3) U.S. Pat. No.6,221,006 issued 24 Apr. 2001 and entitled Entrapping Apparatus AndMethod For Use, (4) International Publication No. WO 99/39648 published12 Aug. 1999 and entitled Entrapping Apparatus And Method For Use, (5)U.S. patent application Ser. No. 09/588,278 filed 5 Jun. 2000 andentitled Tissue Removal Methods And Apparatus, which is now U.S. Pat.No. 6,530,923, (6) International Publication No. WO 00/74561 published14 Dec. 2000 and entitled Tissue Removal Methods And Apparatus, and (7)U.S. patent application Ser. No. 09/844,661 filed 27 Apr. 2001 andentitled Intraoperative Tissue Treatment Methods, which is now U.S. Pat.No. 6,602,204.

BACKGROUND OF THE INVENTION

Cancer presently results in over one thousand five hundred deaths everyday in the United States (550,000 deaths every year). Therapy modalitiesfor cancer are plentiful and continued to be researched with vigor.Still, the preferred treatment continues to be physical removal of thecancer. When applicable, surgical removal is preferred (breast, colon,brain, lung, kidney, etc.). Open, excisional, surgical removal is oftenextremely invasive so that efforts to remove cancerous tissue in lessinvasive ways continue, but have not yet been perfected.

The only cure for cancer continues to be the early diagnosis andsubsequent early treatment. As cancer therapies continue at earlierstages of diagnosis, the cancerous tissue being operated on is alsosmaller. Early removal of the smaller cancers demand new techniques forremoval and obliteration of these less invasive cancers.

There is a variety of techniques that attempt to accomplish lessinvasive cancer therapy, but so far without sufficiently improvedresults. For example, the ABBI system from U.S. Surgical Corporation andthe Site Select system from ImaGyn Corporation, attempt to accomplishless invasive cancer therapy. However, conventional techniques, incontrast with Minimally Invasive Surgery (MIS) techniques, require alarge core (that is more than about 15 mm diameter) incision.Additionally, the Mammotome system from Johnson and Johnson and MIBBsystem from U.S. Surgical Corporation also require large core (overabout 4 mm diameter) access to accomplish biopsy.

A convention held by the American Society of Surgical Oncologists onMar. 13, 2000 reported that conventional stereotactic core biopsy (SCB)procedures fall short in providing definitive answers to detail precisesurgical regimens after this SCB type vacuum assisted biopsy, especiallywith ductile carcinoma in situ (DCIS). Apparently these percutaneoussystems damage “normal” tissue cells so that it is difficult todetermine if the cells are “normal damaged” cells or early pre-cancerous(e.g. Atypical Ductal Hyerplasia (ADH)) cells.

A study presented by Dr. Ollila et al. from the University of NorthCarolina, Chapel Hill, demonstrated that histology and pathology iscompromised using these conventional techniques because of the damagedone to the removed tissue specimens. Hence, for many reasons, includingthe fact that DCIS is becoming more detectable and hence more prevalentin breast cancer diagnosis in the U.S., there is a growing need toimprove upon conventional vacuum assisted core biopsy systems.

SUMMARY OF THE INVENTION

A first aspect of the invention is directed to a tissue localizing andseparating assembly comprising a tissue separator assembly, an elongatecoupler and a tissue localization assembly. The tissue separatorassembly comprises a shaft and a tissue separator device with a distalseparator part movable between retracted and operational states. Theelongate coupler extends through the shaft and has a distal coupler end.The tissue localization assembly has a radially-expandable localizationdevice at its distal end. The distal end of the coupler and the proximalend of the localization assembly may be joined together and moved intothe catheter assembly thereby docking the tissue localization assemblyto the tissue separator assembly.

A second aspect of the invention is directed to a method for docking atissue separator assembly to a tissue localization assembly. Alocalization device of a tissue localization assembly is directed alonga tissue track to a position at a target site. The localization deviceis changed to a radially-expanded state. A distal end of an elongatedcoupler is joined to the proximal end of the tissue localizationassembly, the coupler passing through a catheter assembly of a tissueseparator assembly. The joined proximal and distal ends are moved intothe catheter assembly thereby docking the tissue localization assemblyand the tissue separator assembly.

A third aspect of the invention is directed to a tissue-surroundingassembly comprising an elongate actuator element having a distal end anda tubular braided element. The tubular braided element comprises a bodyhaving a first end, mounted to the distal end of the elongate actuatorelement, and an open second end. The body is a radially expandable andcontractible body having a trumpet-shape when in a relaxed state. Thesecond end flares outwardly when the body is in the relaxed state.

A fourth aspect of the invention is directed to a method for making atissue-surrounding assembly. A tubular braided element, having first andsecond end portions, is selected. A section of the tubular braidedelement is radially expanded, such as over a mandrel. A flexiblematerial is applied to the first end portion, including a part of theradially expanded section, of the expanded tubular braided element. Theflexible material may be applied by dipping the first end portion into aliquid material, with the tubular braided element on the mandrel, andthen curing the liquid material to create the flexible material. Thesecond end portion is directed into the first end portion to create amulti-wall tubular braided element with an inner end and an open outerend. The inner end is secured to an elongate actuator element.

A fifth aspect of the invention is directed to a tissue-penetratingassembly comprising a tissue-penetrating subassembly comprising asupport assembly and a tissue-penetrating device, typically a needle,mounted to and extending from the support assembly. Thetissue-penetrating device comprises a tissue-separating surface,typically the tip of the needle. The tissue-penetrating assembly alsocomprises a tissue-energizing circuit comprising an energy source and aforce-sensitive switch selectively coupling the tissue separatingsurface to the energy source. The force-sensitive switch is operablycoupled to the tissue-penetrating subassembly so that when a drivingforce applied to the tissue-penetrating device exceeds a level, theswitch closes permitting energy from the energy source to reach thetissue separating surface, thereby aiding passage of thetissue-penetrating device through the tissue.

Other features and advantages of the invention will appear from thefollowing description in which the preferred embodiments have been setforth in detail in conjunction with the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a partially schematic overall view of a tissue separatorassembly made according to the invention with portions of the handleremoved for clarity;

FIG. 1A is a simplified cross-sectional view taken along line 1A-1A ofFIG. 1 showing the engagement of a pin within a slot in the lead nutmounted to the lead screw;

FIG. 2 is schematic view of portions of the drive elements of theassembly of FIG. 1;

FIG. 3 is a simplified cross-sectional view of the catheter assemblytaken along line 3-3 of FIG. 1;

FIG. 4 is an oblique view of the housing half of FIG. 1 together withthe drive screw, drive nut and an L-shaped actuator connected to andmovable with the drive nut;

FIGS. 5 and 6 show the handle and catheter assembly of FIG. 1 after theactuator has moved from the position of FIG. 1 and the actuatorextension has pushed the separator wire pusher screw in a distaldirection causing the separator wire to move radially outwardly;

FIG. 7 is a simplified the end view of the block and the pusher screwjust after the pusher screw has exited the slot in the block showing theoff-vertical orientation of the pusher screw;

FIG. 8 illustrates the proximal end of the lead screw, which is visiblefrom outside the housing, and a rotary position indicator marked thereoncorresponding to the position of the separator wire in FIG. 10;

FIGS. 9 and 10 illustrate the structure of FIGS. 5 and 6 after the drivescrew has moved the actuator distally causing the lead nut to rotate thelead screw, catheter shaft and separator wire therewith about 540degrees to create a separated tissue section;

FIGS. 11 and 12 illustrate the manual actuation of tissue sectionholding elements;

FIG. 13 is a simplified view of certain of the components of FIG. 12;

FIG. 14 is a cross-sectional view of the catheter taken along line 14-14of FIG. 13;

FIGS. 15 and 16 illustrate the manual actuation of a tubular braidedelement to surround the separated tissue section;

FIG. 17 is a simplified view of certain of the components of FIG. 16;

FIG. 18 is enlarged side view of the distal end of an alternativeembodiment of the catheter assembly of FIG. 1;

FIG. 19 is a side view of a modified embodiment of the distal end of thecatheter assembly of FIG. 18;

FIG. 20 is a schematic illustration showing the difference in sizebetween the separated tissue sections of the embodiments of FIGS. 18 and19;

FIG. 21 is an enlarged top view taken along line 21-21 of FIG. 18;

FIG. 22 is an enlarged cross-sectional view taken along the line 22-22of FIG. 21;

FIG. 23 is a cross-sectional view taken along line 23-23 of FIG. 18;

FIGS. 24A-24H are simplified side views of different embodiments of theguide element/transition surface of FIG. 18;

FIG. 25 is an overall view of the distal end of the catheter assembly ofFIG. 18 illustrating a hook wire/tissue holding element in a deployedcondition;

FIG. 26 is a cross-sectional view of a portion of the shaft of FIG. 25;

FIG. 27 is a somewhat simplified cross-sectional view of the structureof FIG. 25 with the separator wire portion in a radially retractedstate;

FIG. 27A is a somewhat simplified cross-sectional view of the structureof FIG. 25 with the separator wire portion in a radially extended state;

FIG. 28 illustrates a further embodiment of the invention of FIG. 18including three separator wire portions, one of which is shown in theoperational state; and

FIG. 29A is a simplified end view of the structure of FIG. 28 suggestingthree equally-spaced separator wire portions, each in their retractedstates;

FIG. 29B is a view similar to FIG. 29A but with one separator wireportion in an operational state;

FIG. 30 is a simplified schematic illustration of a tissue-penetratingassembly;

FIG. 31 is an overall view of a tissue localizing and separatingassembly made according to the invention including a tissue separatorassembly, a coupler and a tissue localization assembly, the localizationdevice of the tissue localization assembly being in an expandedcondition at a target site within a patient;

FIG. 32 is an enlarged view of a portion of the assembly of FIG. 31illustrating a loop at the distal end of the coupler being engaged withthe proximal end of the tissue localization assembly;

FIGS. 33 and 34 illustrate the distal end of the coupler and theproximal end of the tissue localization assembly of FIG. 31 joined toone another;

FIG. 35 illustrates the distal movement of the tissue separator assemblycausing the joined ends of FIGS. 33 and 34 to be moved into the catheterassembly thereby docking the tissue localization assembly to the tissueseparator assembly;

FIGS. 35A-35C are simplified drawings showing the movement of anindicator tube, secured to the elongate coupler, through an opening inthe proximal end of the handle;

FIG. 36 is an enlarged view of the distal portion of the assembly ofFIG. 35 after the separator wire portion has been radially expanded androtated and after the hook wire has been deployed to engage theseparated tissue section;

FIG. 37 illustrates the assembly of FIG. 36 after the catheter assemblysleeve has been moved proximally a short distance to expose the distalend of the tubular braided element;

FIG. 38 is a somewhat idealized illustration of the movement of thetubular braided element in a distal direction within a patient with thetubular braided element initially generally following the outline of theseparated tissue section and its outer end generally axially alignedwith the localization device;

FIG. 39 illustrates the assembly of FIG. 38 after having been removedfrom the patient with the outer end of the tubular braided elementreturned to its relaxed state;

FIG. 40 illustrates the shape of a tubular braided material after it hasbeen stretched over a cylindrical mandrel having an enlarged centralportion;

FIG. 41 illustrates the structure of FIG. 40 after one end of themandrel and the tubular braided material has been dipped into a siliconecompound;

FIG. 42 illustrates the open mesh end of the dipped tubular braidedmaterial, after the silicone has been cured and removed from themandrel, being pulled back into the dipped end to create a tubularbraided element;

FIG. 43 illustrates the resulting tubular braided element being mountedto the distal end of the actuator tube;

FIG. 44 shows the proximal end of the tubular braided element beingsecured to the distal end of the actuator tube by a length of heatshrink tubing; and

FIG. 45 illustrates the tubular braided element secured to the actuatortube.

DESCRIPTION OF THE SPECIFIC EMBODIMENTS

FIGS. 1 and 2 illustrate a tissue separator assembly 10 used to separatetarget tissue from surrounding tissue, typically within a patient'sbreast. The removal of target tissue may be for diagnostic ortherapeutic purposes. The assembly 10 includes a catheter assembly 12extending from a handle 14. Introduction of catheter assembly 12 intothe patient, typically through the skin, is preferably aided by the useof, for example, a trocar or an RF tip to provide a suitable paththrough the tissue. A stepper motor 16 is connected to handle 14 by adrive cable 18 and a drive cable connector 20 mounted to the handlehousing 22. Note that in the Figs. only one-half of handle housing 22 isshown; the other housing half is substantially similar. RF energy issupplied to catheter assembly 12 from an RF source 24, along drive cable18 and to the interior of handle 14. A controller 26 controls theoperation of stepper motor 16 as well as RF source 24, such as speed ofoperation and energy level. Controller 26 also receives appropriatefeedback signals from handle 14 and catheter assembly 12, such as tissuetemperature, resistance force. signals, tissue impedance, rotaryorientation, and so forth.

Drive cable 18 is connected to and rotates a drive screw 28 rotatablymounted within handle 14 at a fixed axial location by drive screwsupports 30, 32. A drive nut 34 is threadably mounted to drive screw 28.An L-shaped actuator 36 is secured to drive nut 34. Actuator 36, seeFIG. 4, includes a generally horizontal base portion 38 and a generallyvertical upright portion 40 sized and configured to move within handle14 parallel to the axis of drive screw 28. Therefore, rotation of drivescrew 28 by stepper motor 16 causes actuator 36 to slide within housing22 from the initial position of FIG. 1 to the position of FIG. 10.Reverse and reciprocating movement is also possible.

Catheter assembly 12 includes in introducer sheath 42 mounted to andextending from housing 22. Catheter assembly 12 also includes anactuator tube 43, discussed below with reference to FIGS. 14-17, passingthrough sheath 42 and a shaft 44 passing through tube 43. See FIG. 3.Shaft 44 has a distal portion 46 extending distally of the distal end 48of sheath 42 and a proximal portion 50 extending into the interior ofhandle 14. Proximal portion 50 is secured to and rotates with a leadscrew 52. Accordingly, shaft 44 rotates with lead screw 52. Lead screw52 is mounted within housing 22 in a manner so that it can rotate butnot move axially within housing 22. A tissue separator device 54 extendsalong shaft 44 and has a separator wire portion 56 secured to the distalend 58 of shaft 44. The separator wire 56 is positioned externally ofdistal portion 46. The majority of tissue separator device 54 is in theform of a wire and extends through an axial bore 60 formed in shaft 44.The separator device 54 has a radially extending pusher screw 62 at itsproximal end. The proximal end of shaft 44 has an axially extending slot64, see FIG. 2, through which pusher screw 62 extends. Accordingly,pushing pusher screw 62 distally, that is to the left in the FIGS.,causes tissue separator wire 56 to move outwardly from its radiallycontracted condition of FIG. 1 to its radially extended condition ofFIGS. 5 and 6. This radially outwardly movement is typicallyaccomplished at the target site within the patient, typically apatient's breast. To aid movement of separator wire through the tissue,wire 56 is supplied with RF energy from RF source 24. Other applicationsof energy, such as mechanical reciprocation or mechanical vibration, canalso be used.

The axial movement of pusher screw 62 is caused by the axial movement ofactuator 36. Actuator 36 has an extension 66 extending distally fromupright portion 40. Extension 66 has a downwardly formed distal end 68aligned with pusher screw 62. The initial axial movement of actuator 40,caused by the rotation of drive screw 28 by stepper motor 16, closes asmall gap 70 (see FIG. 2) between distal end 68 and pusher screw 62.This small gap permits the initiation of an electrosurgical arc prior tothe outwardly radial movement of separator wire 56. Continued distalmovement of actuator 36 moves pusher screw 62 distally causing separatorwire 56 to bow outwardly to the position of FIGS. 5 and 6. FIGS. 5 and 6(but not FIG. 1) show the use of a support block 72, which is a part ofhousing 22, to support the distal end of lead screw 52 and the proximalend of shaft 44. Support block 72 has an axially extending slot 74, seeFIGS. 5 and 7, which initially houses pusher screw 62. At the timeseparator wire 56 is fully extended, pusher screw 62 exits slot 74 andthe distal end 68 of extension 66, which has a chamfered face, causespusher screw 62, along with shaft 44, to begin rotating to theoff-vertical position of FIG. 7. At the same time upright portion 40 ofactuator 36 closes gap 73 (see FIG. 2) and contacts a lead nut 75threadably mounted on lead screw 52. An anti-rotation pin 76 extendsfrom upright portion 40 of actuator 36 and is housed within a U-shapedslot 78 formed in lead nut 74, see FIG. 1A, to prevent lead nut 74 fromrotating around lead screw 52 as lead nut 74 it is moved axially byactuator 36. Instead, the axial movement of actuator 36 causes leadscrew 52 to rotate thus rotating shaft 44. Assembly 10 is configured sothat shaft 44 rotates about 540 degrees to ensure a tissue section 80 iscompletely separated from the surrounding tissue by the passage ofseparator wire 56 through the tissue. The radial position of separatorwire 56 can be easily determined by looking at the proximal end 82 oflead screw 52, which is exposed through housing 22. See FIG. 8. Proximalend 82 has a rotary position indicator 84 formed thereon correspondingto the rotary position of separator wire 56.

The above-described sequence of events, according to this disclosedembodiment, proceeds automatically once initiated by a user. Of courseoperation of the device, including one or more of extension of separatorwire 56, rotation of shaft 44 and energizing wire 56, can be terminatedmanually or automatically based on, for example, an unexpectedresistance to the rotation of shaft 44.

Assembly 10 also includes a T-pusher device 86 having a pair of pushertabs 88 extending laterally outwardly from slots formed in housing 22.See FIGS. 11-13. After shaft 44 has completed its rotation, the userbegins pushing tabs 88 distally. This causes an extension 90 of device86 to rotate a flipper cam 92 about a pivot pin 94; flipper cam 92 isconnected to the proximal ends of a pair of tissue section holdingelements 96. Holding elements 96 are in the form of wires passingthrough axial bores 98 formed in shaft 44 as shown in FIG. 3. The distalends of holding elements 96 are preformed hook wires 100, preferablymade of a shape memory material such as Nitinol, which pass throughopenings formed in distal portion 46 of shaft 44 and engage separatedtissue section 80 to help secure tissue section 80 to distal portion 46of shaft 44.

Device 86 includes a distal end 102 connected to the proximal end ofactuator tube 43. Thus, the movement of device 86 causes tube 43 to movedistally within introducer sheath 42. At this point, that is with hookwires 100 deployed as an FIGS. 11-13, a tubular braided element 104, seeFIGS. 14-17, secured to the distal end of actuator tube 43, is stillfully housed within sheath 42. Further distal movement of device 86causes tubular braided element 104 to extend outwardly past distal end48 of sheath 42 to the position of FIGS. 15-17. The purpose of tubularbraided element 104 is to surround separated tissue section 80 bypassing along the dissection plane between the separated tissue sectionand the surrounding tissue. The open outer end 106 of element 104naturally expands radially as it is pushed axially through the tissue.To aid the proper initial radial expansion of element 104, shaft 44 hasan outwardly tapered guide surface 108, formed on a guide element 110,positioned adjacent to distal end 48 of introducer shaft 42. The properradial expansion of element 104 may also be aided by the shape thatelement 104 takes when in its relaxed state. See, for example, thediscussion of tubular braided element 104 with regard to FIGS. 40-45.Guide element 110 has a slot in its proximal surface into which theproximal end of separator wire 56 passes when in the radially expandedcondition of FIG. 9; this helps to keep separator wire 56 from foldingover during rotation. If desired, outer end 106 of tubular braidedelement 104 could include a drawstring or other type of closure element.The separated tissue section 80, now substantially enclosed withintubular braided element 104 and secured to distal portion 46 of shaft 44by hook wires 100, may be removed from the patient.

With the present invention separated tissue section 80 retains most ifnot all of its physical integrity once removed from the patient. Also,the use of tubular braided element 104, especially when it is sealed orotherwise impermeable to the passage of material, helps to reduce thepossibility of seeding diseased tissue along the tissue track duringremoval of separated tissue section 80.

FIGS. 18-29B illustrate further embodiments of the invention with likereference numerals referring to like elements. FIG. 18 is an enlargedside view of the distal end 120 of alternative embodiment of thecatheter assembly 12 of FIG. 1. Referring now also to FIGS. 21, 22 and27, separator wire portion 56 is seen to include a distal end 122.Distal end 122 terminates at a ball-type element 124 (see FIG. 22)housed within a cavity 126 defined within distal portion 46 of shaft 44at the tip 136 of the distal portion to form a pivot joint 128. Theprovision of pivot joint 128 permits distal end 122 to effectively pivotfreely as separator wire portion 56 is moved between the operational andretracted states. In addition to reducing stresses and improving thefatigue characteristics of distal end 122 of separator wire portion 56,the use of pivot joint 128 helps to increase the volume of the separatedtissue section removed from the patient for the same distance of travelof tissue separator device 54. This increase in volume may beappreciated by comparing the embodiments of FIGS. 18 and 19. In the FIG.19 embodiment, the distal end 122 of separator wire portion 56 isrigidly or otherwise non-pivotally secured to distal portion 46 of shaft44. FIG. 20 illustrates the increased volume of separated tissue section80A resulting from the embodiment of FIG. 18 to the reduced volume,separated tissue section 80B from the embodiment of FIG. 19. In thisexample the volume of separated tissue section 80A has been calculatedto be about 50 percent greater than the volume of separated tissuesection 80B for the same distance of travel of tissue separator device54.

Distal portion 46 of shaft 44 includes guide element 110 which acts as atransition surface 110. Transition surface 110 is a distally-facingsurface extending radially outwardly and proximally, that islongitudinally away from the tip 136 of distal portion 46. A series ofspaced-apart, first, proximal energizable tissue separator elements 130are positioned along transition surface 110. FIG. 23 is across-sectional view taken along line 23-23 of FIG. 18 and illustratesthe electrical connection of elements 130 to metallic tube 132.

FIGS. 24A-24H illustrate alternative embodiments of first elements 130.Elements 130A have extended longitudinal lengths, as compared with theessentially circular elements 130 of FIGS. 18 and 23. It is believedthat the extended lengths of element 130A may be useful for reducing thepenetration force needed for placement at the target site. The FIG. 24Aembodiment is the presently preferred embodiment. Element 130B comprisesa circumferentially continuous or substantially circumferentiallycontinuous element. The circumferentially extending element 130B mayalso be useful for reducing the required penetration force. Elements130C are similar to elements 130 but are located at peripheral region140 of transition surface 110. Elements 130D and 130E, shown in FIGS.24D and 24E, are generally V-shaped and serpentine-shaped variations.Elements 130F and 130G, shown in FIGS. 24F and 24G, extend alongsubstantially the entire lengths of distal portion 46 in straight andspiral configurations, respectively. FIG. 24H illustrates a furtherembodiment of elements 130H with elements 130H extending radiallyoutwardly from distal portion 46; elements 130H may be retractable andmay have shapes other than the pointed, triangular shape illustrated.While elements 130 are typically formed from metal wires or similarstructure, elements 130 may also be painted, plated or otherwisedeposited on the surface of distal portion 46. A combination of two ormore of the arrangements of element 130 may be useful in appropriatecircumstances. While presently all of elements 130 are supplied withequal energy levels, different energy levels may be supplied. Also, theenergy levels supplied may be varied over time or according to theresistance to the passage of separator wire portion 56 through thetissue. Also, energy to elements 130 may be turned on as needed at thediscretion of the user.

Distal portion 46 is hollow and contains an electrically conductive,metallic tube 132 defining an opening 134 at the tip 136 of distalportion 46. The outer, annular edge of tube 132 acts as a second, distalenergizable tissue separator element 138. Both first element 130 andsecond element 138 are selectively coupleable to one or more appropriateenergy sources to aid movement of distal portion 46 through tissue tothe target site.

FIGS. 25 and 26 illustrate the hook wires 100, which act as tissueholding elements, extending through openings 142 formed within distalportion 46 of shaft 44. Hook wires 100 are preferably sized, positionedand shaped to engage separated tissue section 80 at about its center ofmass. While two hook wires 100 are shown in this embodiment, a greateror lesser number may also be used. Also, hook wires 100 having differentsizes and shapes may be used. Hook wires 100 may also be located atdifferent axial positions and may be energizable to aid movement throughtissue.

FIGS. 25, 27 and 27A illustrate the passage of separator wire portion 56through proximal and distal channels 146, 148 formed in distal shaftportion 46. Distal portion 46 defines a base surface 150 extending alongthe bottoms of channels 146 and 148 and extending between channels 146and 148. Separator wire portion 56 lies against base surface 150 when ina retracted state. As shown best in FIGS. 27 and 27A, the centralportion 152 of base surface 150 is convex so that when separator wireportion 56 is in the retracted state, a central portion of wire portion56 lies along a convex line, that is a line that bows slightlyoutwardly. Therefore when tissue separator device 54 is moved distally,separator wire portion 56 is predisposed to move radially outwardly inthe desired manner. The amount of force needed to be applied to device54 may also be reduced by the use of convex central portion 152.

FIG. 28 illustrates a further alternative embodiment to the embodimentof FIG. 18 comprising three separator wire portions 56, as opposed toone in FIG. 18, one wire portion 56 being shown in an operational stateand the other two wire portions 56 in retracted states and adjacent basesurfaces 150. This is suggested in FIG. 29B. Another difference from theembodiment of FIG. 18 is that the function of first, proximalenergizable tissue separator elements 130 has been replaced byenergizing the three separator wire portions 56 when the device isdirected through tissue to a target site with wire portions 56 inretracted states. This is suggested in FIG. 29A. Once at the target sitethe physician may decide to move one, two or all three of separator wireportions 56 from the retracted state to the operational state dependingon various factors, such as the characteristics of the tissue and thenumber of pieces tissue section 80 is to be divided into.

Distal portion 46, in the embodiment of FIGS. 18-29B, comprises aproximal element 154, a body portion 156 and tip 136, tip 136 acting asan end cap. FIG. 27 illustrates the interengagement of elements 154, 156and 136. Elements 154, 156 and 136 are configured to promote simpleassembly. Assembly may take place by simply stacking each element inorder over central tube 132, the parts being held in place distally bythe flared end 138 of the tube. Elements 154, 156 and 136 are preferablyelectrically non-conductive. Elements 154 and 156 are typically madefrom the medical grade ceramic material, such as Al₂O₃ or zirconia,while tip 136 is typically made from a medical grade polymer, such asPEEK or polyimide.

The amount of force required for the passage of a needle, or othertissue-penetrating element, such as distal portion 46 of shaft 44,through tissue often changes because the tissue characteristics oftenchanges between the point of entry and the target site. If thetissue-penetrating element must pass through a hard or otherwisedifficult-to-penetrate tissue region, the amount of force needed topenetrate the hard tissue region may be sufficiently great to, forexample, cause the tissue-penetrating element to buckle. Even if thetissue-penetrating element has sufficient columnar strength to resistbuckling, the amount of force required may be sufficient to cause thetissue to be deformed making it difficult to position the tip of thetissue-penetrating element at the target site. Also, once the tip haspassed through the difficult-to-penetrate tissue region, the amount offorce needed to do so may tend to cause the tip of thetissue-penetrating element to be inserted much farther than desiredcausing unintended tissue trauma and possibly injuring adjacent organs.

FIG. 30 illustrates, in schematic form, a tissue-penetrating assembly160 comprising broadly a tissue-penetrating subassembly 162 coupled to atissue-energizing circuit 164 and a force-sensitive switch 166 operablycoupled to the tissue-penetrating subassembly. The subassembly 162comprises a handle assembly 168, or other support assembly, including ahandle 170, a handle extension 172 extending rigidly from handle 170,and a needle clamp 174 mounted to handle 170 at a pivot 176. Subassembly162 also includes a needle 178, or other tissue-penetrating device,secured to and extending from needle clamp 174. Needle 178 includes aneedle shaft 180 covered by electrical insulation 182 along most of itslength. Electrical insulation 182 helps to concentrate thetissue-penetrating energy at the tip 184 of needle 178, tip 184 having atissue-separating surface 185.

Force-sensitive switch 166 includes a compression spring 186 capturedbetween needle clamp 174 and handle extension 172. Assembly 160 alsoincludes an arming switch 188 mounted to handle 170, switch 188including an arm 190 mounted to handle 170 at a pivot 192. Switch 188also includes an arming compression spring 194 captured between arm 190and handle extension 172. The use of arming switch 188 helps to enhancethe safety of assembly 160 by helping to prevent the inadvertentconnection of arm 190 to needle clamp 174, which would signal RFgenerator 200 to apply RF energy between RF signal 196 and return signal202. Circuit 164 includes lead 196 electrically connected to needleclamp 174, and thus needle tip 184. Circuit 164 also connects signal 198to arm 190 through pivots 176, 192, respectively. Circuit 164 alsocomprises an RF generator 200, from which leads 196, 198 extend, and areturn cable 202 coupling generator 200 to a return pad 204. Anelectrical conductor 206 is mounted to handle extension 172 and haselectrical contact surfaces 208, 210 positioned opposite thecorresponding surfaces of needle shaft 180 and arm 190. An arming button212 is mounted to arm 190 to permit the user to arm assembly 160 bypressing an arming button 212 to cause arm 190 to contact surface 210.With the device now armed, needle 178 is directed into tissue,exemplified by three layers of tissue, including soft tissue layers 214and 218 and hard or otherwise difficult-to-penetrate tissue layer 216.Upon encountering hard tissue layer 216, the force needed to penetratetissue layer 216 is sufficient to compress spring 186 and cause needleshaft 180 to contact electrical contact surface 208 thus completing thecircuit between signal 196 and signal 198 of RF generator 200. RFgenerator 200 will then supply energy to surface 185 at tip 184permitting needle 178 to pass through hard tissue 216 without excessiveforce. Once tip 184 has passed through hard tissue layer 216, the forceon needle 178 decreases to permit spring 186 to separate needle shaft180 from contact surface 208 so to stop supplying RF energy to tissueseparator surface 185.

Tissue-penetrating assembly 160 can be used to aid the insertion of asimple needle into tissue. However, the tissue-penetrating inventionalso can be incorporated into other devices including tissue-penetratingelements, such as the embodiments discussed above including shaft 44 anda target tissue localization device disclosed in U.S. Pat. No.6,179,860.

FIGS. 31-39 illustrate further aspects of the invention in which tissueseparator assembly 10 is combined with an elongated coupler 220 and atissue localization assembly 222 to arrive at a tissue localizing andseparating assembly 224. Tissue localization assembly 222 may be of thetype disclosed in U.S. Pat. No. 6,179,860. Assembly 222 is showndeployed within a patient 226 with localization device to 112 in aradially expanded, deployed condition. Assembly 222 includes a sheath228 (see FIG. 32) within which a pull wire 230 is slidably housed. Therelative axial movement of sheath 228 and pull wire 230 causeslocalization device 112 to radially expand and radially contract. Theproximal end 232 of pull wire 230 is a recurved end 232 (see FIGS. 32,34) for engagement by coupler 220 as discussed below.

Coupler 220 is a flexible wire having a coupler loop 234 at its distalend and an enlarged proximal end 236. Coupler 220 passes through shaft44 (see FIGS. 2, 32) of catheter assembly 12. Coupler loop 234 is usedto join coupler 220 to the recurved end 232 of pull wire 230; this isshown in FIGS. 31-34. After being so joined, tissue separator assembly10 is moved distally along coupler 220, while the user grasps end 236 tomaintain tension on the tissue localization assembly 220, causing thejoined ends 232, 234 to pass into shaft 44 thus docking tissuelocalization assembly 222 to tissue separator assembly 10. Continueddistal movement of assembly 10 causes catheter assembly 12 to enterpatient 226 and pass along the tissue track created by tissuelocalization assembly 222 until tip 136 of distal portion 46 of shaft 44is properly positioned relative to localization device 112. Properpositioning is visually indicated to the user by a length of tube 233,typically colored red and affixed to coupler 220, becoming exposed afterexiting the proximal end opening 235 of handle 14 as shown in FIGS.35A-35C. When properly positioned, see FIG. 35C, a locking spring clip237, located on handle 14 adjacent to proximal end opening 235, springsback from its biased position of FIG. 35B to its unbiased position ofFIGS. 35A and 35C to prevent tube 237 from inadvertently reenteringhandle 14. When so positioned, tissue localization assembly 222 becomesat least temporarily locked or fixed to tissue separator assembly 10 toprevent the inadvertent relative axial movement between localizationdevice 112 and assembly 10. Of course other locking mechanisms, such asa spring finger carried by assembly 220 and engageable with handle 14,can also be used to lock assemblies 10, 222 to one another.

FIG. 36 is an enlarged view of the distal portion of assembly 224 ofFIG. 35 after separator wire portion 56 has been radially expanded androtated, to create a separated tissue section 80, and after hook wire100 has been deployed to engage the separated tissue section 80. It hasbeen found to be desirable to leave a space, indicated generally asdistance 238, between localization device 112 and separated tissuesection 80. FIG. 37 illustrates the assembly of FIG. 36 after introducersheath 42 has been moved proximally a short distance to expose outer end106 of tubular braided element 104. FIG. 38 is a somewhat generalizedillustration of the movement of tubular braided element 104 in a distaldirection within patient 226 with the tubular braided element initiallygenerally following the outline of separated tissue section 80 and outerend 106 generally axially aligned with localization device 112. Itshould be noted that the movement of outer end 106 of tubular braidedelement 104 will generally following the path indicated until it reachesposition 240. Following position 240, the path outer end 106 takes willlargely depend on the physical characteristics of the tissue throughwhich is passing. However, the path illustrated is typical. Separatedtissue section 80 is then removed from patient 226 by simultaneouslypulling the entire assembly shown in FIG. 38, including separated tissuesection 80 captured by tubular braided element 104 and localizationdevice 112, secured by coupler 220, back along the tissue track. Duringthis movement tubular braided element 104 has a tendency to elongateaxially to a reduced diameter, more cylindrical form thus reducingpotential tissue trauma along the tissue track and through the accessopening at the beginning of the tissue track.

FIG. 39 illustrates the assembly of FIG. 38 after having been removedfrom patient 226 with outer end 106 of tubular braided element 104returned to its relaxed state and tissue specimen 80 retained by tubularbraided element 104 and localization device 112. As suggested in FIG.39, tubular braided element 104, when in a relaxed state, has agenerally trumpet shape with outer end 106 flaring outwardly. It hasbeen found that this trumpet shape helps to guide tubular braidedelement 104 around separated tissue section 80, especially during itsinitial movement from introducer sheath 42.

FIGS. 40-45 illustrate a preferred method of making tubular braidedelement 104. Tubular braided element 104 is sized according to the sizeof the tissue specimen being removed so that the number of elements,sizes and other specifications discussed below may be varied accordingto a particular circumstance. FIG. 40 illustrates the shape of a lengthof tubular braided material 244 after it has been stretched over acylindrical mandrel (not shown) having an enlarged (20.5 mm diameter by50 mm long) central portion in this embodiment. Material 244, prior tobeing stretched over the mandrel, is supplied in a continuous length andcut to size for the mandrel and a starting diameter of 5/16″ or ˜8 mm.Material 244 is made of monofilament polyester fibers having a diameterof 0.10 inch (0.25 mm) The braid consists of 56 monofilaments and ismade on 56 carrier braider. The braid, when formed in continuouslengths, maintains an approximate 5/16″ (8 mm) internal diameter. Thebraid angle is held fixed during the braiding operation, and was chosenfor this application because a small shortening in axial length resultsin a rapid change in diameter. The enlarged central portion of themandrel corresponds to the shape of tubular braided material 244, thatis it is cylindrical with generally hemispherical ends. FIG. 41illustrates the structure of FIG. 40 after one end of the mandrel andtubular braided material 244 has been dipped into a silicone compound.The dipped structure is then cured, typically in an oven, to create asilicone film or web 246 covering one end of tubular braided material244. After curing, the dipped, cured structure 248 is removed from themandrel by being pulled over the mandrel from left to right in FIG. 41.FIG. 42 illustrates the open mesh end 250 of the dipped, cured structure248 being pulled back into the dipped end to create the dual-walltubular braided element 104 shown in FIG. 43. FIG. 43 illustratestubular braided element 104 being mounted to the distal end of actuatortube 43. FIGS. 44 and 45 show the proximal end of tubular braidedelement 104 being secured to the distal end of actuator tube 43 by alength of heat shrink tubing 252 and an adhesive to create atissue-surrounding assembly 254. Dual-wall tubular braided element 104has an outer wall 256 substantially completely covered with silicone web246, and inner wall 258 at least substantially free of the silicone webmaterial, an open outer end 106 covered with silicone web 246.

Silicone web 246 serves at least two functions. It helps maintain thetrumpet shape of tubular braided element 104 in its relaxed state whilepermitting the tubular braided element to radially expand and radiallycontract from the trumpet shape. It also helps to prevent passage oftissue through tubular braided element 104 during removal of separatedtissue section 80. This helps to prevent contamination along the tissuetrack during tissue removal procedures. While tubular braided element104 could be made as a single layer, that is without open mesh end 250being pulled back into the structure, it has been found that doing sohelps to maintain a softer leading edge at outer end 106 of tubularbraided element 104. The general trumpet shape shown in FIGS. 43-45occurs as a natural result of the forming process illustrated anddescribed.

The following discussion of the development of the current embodiment ofbraided element 104 may be useful in appreciating its various featuresand advantages. The presently preferred embodiment of braided element104 comprises a tubular sleeve of braided polyester (PET—polyethyleneterephthalate) monofilament folded over itself to form a smooth end. Theopen weave construction allows it to enlarge to several times itsoriginal diameter. The outer braided layer is coated with silicone.

Early braided element prototypes consisted of Nitinol braided tubing.The wire diameter, braid angle and number of wires that comprise thebraid were explored. These properties affect the strength of the braidedelement. The braided element must have enough stiffness and columnarstrength to overcome the forces acting against it as it is deployed inthe tissue. However, if it is too rigid, it may push the separatedtissue section further into the cut cavity. Non-braided forms were alsoconsidered, such as Nitinol wire placed axially along the lengths of theaxis, supported by coating or other rigid members. The combination ofwire diameter, braid angle, and number of wires also affects theretracted properties of the braided element. In its undeployed state,the braided element was designed to fit inside a 6 mm sheath. Some ofthe Nitinol prototypes that were fabricated seemed to have adequatestrength and stiffness, and fit within a 6 mm sheath. However, becauseof other factors discussed below, a PET braid presently preferred over aNitinol braid.

There are several factors that interact to effect columnar strength.Braid angle, number of filaments, and filament material stiffness anddiameter are the main determinants. Axial orientation, greater numberand stiffer filaments all combine for greater columnar strength. Thepresently preferred material for braided element 104 is 0.010″ (0.25 mm)diameter monofilament. The number of monofilaments in the braid waschosen to optimize the mechanical properties of braided element 104.Increasing the number of filaments will create the opposite effect—thecolumnar strength will be reduced thus increasing the chance ofbuckling. Fewer filaments creates an increase in spacing between thefilaments as the braided element expands from retracted to deployed. Ifthe spacing becomes too large, the coating may tear. Also, a braidedelement constructed with a more axially oriented braid angle will takeup much more length in the retracted state and therefore require agreater amount of travel to deploy. The number of filaments was chosento optimize braided element strength, spacing between filaments, andamount of deployment travel.

It is presently preferred that the distal end of the braided element,that is the end that first comes into contact with the tissue, besmooth. It was discovered at a braided element with jagged or sharp edgemay get caught in the tissue and fail to slide into the cut tissueinterface around the separated tissue section. For the Nitinol braid,various methods of terminating the lose wires were explored, such assoldering, brazing, or bonding balls at the wire ends, or folding eachsingle wire over. These methods were not very successful. For the ballsto be atraumatic, they need to be of considerable size. The balls orfolded-over ends increase the diameter of the retracted braided element,making it difficult to fit inside a sheath. This led to concepts of‘roll-over’ and ‘double layer’ braided elements. For both concepts, thetubular braid is folded over itself to form a two-layered braidedelement with folded-over, smooth ends. For a ‘double layer’ braidedelement, the two layers are bonded together at the proximal end. Thetwo-layered Nitinol braided elements that were prototyped showedpromising characteristics. However the folded-over ends provided toomuch bulge and made it difficult or impossible to retract into a 6 mmdiameter sheath. The PET braid, on the other hand, forms a nice creasewhen the braid is folded over, and is easily retracted into the sheath.For deployment, the outer layer is pushed forward and allowed to slideover the inner layer. This embodiment has potential but is not thepresently preferred embodiment.

The shape of the braided element also affects its functionality. Braidedelement prototypes of many different shapes were tested, such as“bullet”, “cone”, and “bell” or “trumpet” profiles of varying diameters.A desirable characteristic of braided element 104 is that the braidedelement flares open as it is initially deployed, so that it ispredisposed to expand around the biopsy sample rather than push thesample further into the cavity. The shape of braided element 104 hasbeen optimized to maximize the amount that it flares open duringdeployment.

The braided element is currently coated with a two-component siliconeelastomer. Some polyurethane coatings were investigated also, but didnot perform as well as silicone coatings during preliminary testing. Thesilicone coating was chosen because of its high tear strength andelasticity. From the retracted state to the fully deployed state, thediameter of braided element 104 may expand as much as 300%. The braidedelement may have a snare at the distal end to aid in capturing thesample.

Modification and variation can be made to the disclosed embodimentswithout departing from the subject of the invention as defined in thefollowing claims. For example, lead screw 52 could be hollow to permitactuator shaft 114, or other medical devices, to pass therethrough andinto a lumen within shaft 44. While base surface 150 is shown to have asmoothly curving shape, surface 150 may have other shapes, such as adiscontinuous surface shape, a flat surface shape with one or moreprojections providing the desired bow in the separator wire portion 56,or a combination thereof. Braided element 104 may be made of othermaterials and by other processes than those disclosed.

Any and all patents, patent applications and printed publicationsreferred to above are hereby incorporated by reference.

1. A tissue localizing and separating assembly comprising: a tissueseparator assembly comprising: an elongate tubular member comprising aproximal end, a distal end, and a lumen therebetween; a tissue separatordevice located near the distal end of the elongate tubular member; anelongate coupler extending through the lumen of the elongate tubularmember and having a distal coupler end; and a tissue localizationassembly comprising an elongate member and a localization device,wherein the elongate member has a proximal end and a distal end, andwherein the localization device is located at the distal end of theelongate member; wherein the distal coupler end and the proximal end ofthe elongate member of the tissue localization assembly are joinable toone another to permit the distal coupler end and the proximal end of theelongate member of the tissue localization assembly to be joined andmoved into the lumen of the elongate tubular member thereby docking thetissue localization assembly to the tissue separator assembly.
 2. Theassembly according to claim 1, wherein the tissue separator devicecomprises a distal separator part movable between a retracted state,towards the elongate tubular member, and a radially operational state,away from the elongate tubular member.
 3. The assembly according toclaim 2, wherein the tissue separator assembly further comprises anintroducer sheath within which the elongate tubular member is rotatablymounted and wherein the distal separator part is movable radiallyoutwardly to the operational state.
 4. The assembly according to claim1, wherein the elongate coupler comprises a flexible wire and the distalcoupler end comprises a wire loop.
 5. The assembly according to claim 1,wherein the tissue localization assembly is movable from a first,radially-contracted state to a second, radially-expanded state.
 6. Theassembly according to claim 5, wherein the tissue localization assemblycomprises a hollow sheath housing a pull wire, the pull wire having arecurved end constituting said proximal localization assembly end. 7.The assembly according to claim 1, wherein the tissue separator assemblycomprises a proximal end opening through which the elongate couplerpasses.
 8. The assembly according to claim 1, wherein the tissueseparator assembly further includes a handle, the handle having aproximal end opening.
 9. The assembly according to claim 1, wherein theelongate coupler includes an engagement element engageable with thetissue separator assembly when the distal separator device is adjacentto the localization device.
 10. The assembly according to claim 9,wherein the engagement element comprises a spring element carried by theelongate coupler.
 11. The assembly according to claim 1, wherein thetissue separator assembly comprises: a tissue-energizing circuitcomprising an energy source and a force-sensitive switch selectivelycoupling the tissue separator device to the energy source; and saidforce-sensitive switch operably coupled to the tissue separator assemblyso that when a driving force applied to the tissue separator deviceexceeds a level, said switch closes permitting energy from the energysource to reach the distal end of tissue separator device, therebyaiding passage of the tissue separator device through the tissue.
 12. Amethod for docking a tissue separator assembly to a tissue localizationassembly comprising: providing a tissue separator assembly comprising anelongate tubular member and a tissue separator device, wherein theelongate tubular member comprises a proximal end, a distal end, and alumen therebetween, and the tissue separator device is located near thedistal end of the elongate tubular member; directing a tissuelocalization assembly along a tissue track to a position at a targetsite, the tissue localization assembly comprising an elongate member anda localization device, wherein the elongate member has a proximal endand a distal end, and wherein the localization device is located at thedistal end of the elongate member; changing the localization device froma first, radially-contracted state to a second, radially-expanded state;joining a distal end of an elongate coupler to the proximal end of theelongate member of the tissue localization assembly, the elongatecoupler passing through the lumen of the elongate tubular member of thetissue separator assembly; and moving the joined proximal and distalends into the lumen of the elongate tubular member of the tissueseparator assembly, thereby docking the tissue localization assembly andthe tissue separator assembly.
 13. The method according to claim 12,wherein the joining step comprises engaging a coupler loop at the distalend of the elongate coupler to a recurved element at the proximal end ofthe tissue localization assembly.
 14. The method according to claim 12,wherein the directing step is carried out so that the localizationdevice is directed to a position distal of the target site.